Optical techniques for the measurement of chest compression depth and other parameters during cpr

ABSTRACT

Embodiments of the present invention are related to a method and device for the determination and calculation of the depth of chest compressions during the administration of cardiopulmonary resuscitation (CPR). Embodiments use an optical sensor to monitor the distance that a victim&#39;s chest is displaced during each compression throughout the administration of CPR. The optical sensor is most commonly an image sensor such as a CMOS or CCD sensor, and more specifically a CMOS image sensor capable of three-dimensional imaging based on the time-of-flight principle. An infrared emitter may illuminate the victim&#39;s body and any visible piece of ground beside the victim. As the infrared light interacts with any surfaces it encounters, it is reflected and returns to the image sensor where the time of flight of the infrared light is calculated for every pixel in the image sensor. The distance data is used to gauge the effective displacement of the victim&#39;s chest. The optical sensors can be used to visualize the size of a patient and immediately gauge the body type and instruct the user accordingly. Furthermore, optical measurement techniques can be used to accurately measure chest rise during artificial respiration and ensure that proper ventilation is being administered in between compressions. In addition, optical measurements of the chest of the victim and the hands of the rescuer can be used to help ensure that the rescuer has positioned his or her hands in the anatomically correct location for effective CPR.

CROSS REFERENCE TO RELATED APPLICATIONS

This application is a non-provisional application of and claims benefitfrom U.S. Provisional application 61/227,637, filed Jul. 22, 2009,titled OPTICAL TECHNIQUES FOR THE MEASUREMENT OF CHEST COMPRESSION DEPTHAND OTHER PARAMETERS DURING CPR, which is hereby incorporated byreference.

FIELD OF THE INVENTION

This disclosure generally relates to the measurement of chestcompression depth during the administration of cardiopulmonaryresuscitation (CPR), specifically to compression depth measurement byuse of optical sensors.

BACKGROUND OF THE INVENTION

There are currently an estimated 40,000 incidences of cardiac arrestevery year in Canada, most of which take place outside of hospitalsettings. The odds of an out-of-hospital cardiac arrest currently standat approximately 5%. In the U.S., there are about 164 600 such instanceseach year, or about 0.55 per 1000 population. There is a desire todecrease these out-of hospital incidences of cardiac arrest. Certainplaces, such as sports arenas, and certain classes of individuals, suchas the elderly, are at particular risk and in these places and for thesepeople, a convenient solution may be the difference between survival anddeath.

Cardiopulmonary resuscitation (CPR) is a proven effective technique formedical and non-medical professionals to improve the chance of survivalfor patients experiencing cardiac failure. CPR forces blood through thecirculatory system until professional medical help arrives, therebymaintaining oxygen distribution throughout the patient's body. However,the quality of CPR is often poor. Memory retention of proper CPRtechnique and protocol may be inadequate in most individuals and theanxiety of an emergency situation may confuse and hinder an individualin delivering proper treatment.

According to the journal of the American Medical Association (2005),cardiopulmonary resuscitation (CPR) is often performed inconsistentlyand inefficiently, resulting in preventable deaths. Mere months afterthe completion of standard CPR training and testing, an individual'scompetency at performing effective chest compressions often deterioratessignificantly. This finding was found to hold true for untrainedperformers as well as trained professionals such as paramedics, nurses,and even physicians.

The International Liaison Committee on Resuscitation in 2005 describedan effective method of administering CPR and the parameters associatedwith an effective technique. Parameters include chest compression rateand chest compression depth. Chest compression rate is defined as thenumber of compression delivered per minute. Chest compression depth isdefined as displacement of the patient's sternum from its restingposition. An effective compression rate may be 100 chest compressionsper minute at a compression depth of about 4-5 cm. According to a 2005study at Ulleval University Hospital in Norway, on average, compressionrates were less then 90 compressions per minute and compression depthwas too shallow for 37% of compressions.

According to the same study, CPR was often administered when unnecessaryor was not administered when necessary. The study found thatcompressions were not delivered 48% of the time when cardiovascularcirculation was absent.

Positioning of the hands is another parameter that may be consideredwhen delivering CPR. It has been found that an effective position forthe hands during compression is approximately two inches above the baseof the sternum. Hand positioning for effective CPR may be differentdepending on the patient. For example, for performing CPR on an infant,an effective position may be to use two fingers over the sternum.

Other studies have found similar deficiencies in the delivery of CPR. A2005 study from the University of Chicago found that 36.9% of the time,fewer than 80 compressions per minute where given, and 21.7% of thetime, fewer than 70 compressions per minute were given. The chestcompression rate was found to directly correlate to the spontaneousreturn of circulation after cardiac arrest, so it is very important thatthe optimum rate be achieved for maximum chances of patient survival.

In addition to too shallow compressions, too forceful compressions mayalso be problematic. Some injuries related to CPR are injury to thepatient in the form of cracked ribs or cartilage separation. Suchconsequences may be due to excessive force or compression depth. Onceagain, lack of practice may be responsible for these injuries.

Therefore, a device to facilitate the proper delivery of CPR in anemergency is desired.

Furthermore, a device that can also be used in objectively training andtesting an individual may be useful for the CPR training process andprotocol retention.

Current solutions in emergency cardiac care mostly focus on in-hospitaltreatment or appeal mostly to medical professionals. CPR assist devicesthat tether to defibrillators can be found in hospitals. However, thesedevices are often expensive and inaccessible to the lay individual whodoes not have a defibrillator on hand or cannot operate such a device.Furthermore, such devices are often not portable nor are they easilyaccessible. Simple devices with illuminated bar graph or LED displaysindicating compression force are often cumbersome in design andnon-intuitive in use. Such a device may be uncomfortable to the patientand user and often has minimal data output. Thus, misuse of such adevice is most likely rendering it a hindrance rather than an aid.

There are currently mechanical systems for the delivery of CPR that maybe used in a hospital setting. Chest compression may be deliveredthrough a mechanism including mechanical movement (e.g., piston movementor motor movement). One such device is the AUTOPULSE by Revivant Corp,which has a computer-controlled motor attached to a wide chest band thatcompresses the chest, forcing blood to the brain when the heart hasstopped beating. Such a device is cumbersome and heavy to transport,requires time to set up and activate and is expensive.

U.S. Pat. No. 6,351,671 discloses a device that measures the chestimpedance of a victim as well as the force of active chest compressions.From these calculations, the device indicates to the user when asuccessful compression has been completed. However, this technologyrequires defibrillator pads to be placed across the chest of the victimand is, consequently, relatively time consuming to activate. Thecommercially available device, Q-CPR by Phillips Medical, must beattached to an expensive hospital-grade defibrillator making itexpensive, heavy and inaccessible to the lay user.

U.S. Pat. No. 7,074,199 discloses the use of an accelerometer for themeasurement of compression depth. Any acceleration data fromaccelerometers used to measure the depth of chest compression during CPRis prone to cumulative errors. Consequently, these sensors are notsuitable for highly accurate or detailed data collection regarding CPRparameters and can only be relied on for approximate depth values.Furthermore, the use of an accelerometer in a CPR monitoring devicewithout an external reference is prone to error if the patient orrescuer is mobile. For example, if the patient is being medicallytransported in an ambulance, helicopter or on a gurney, theaccelerometer is unable to differentiate between the external movementof the patient and the compressions of the chest. In any type ofnon-stationary environment, an accelerometer based device is unreliableand ineffective. The use of an accelerometer to calculate compressiondepth also relies on complicated and error-prone calculations tocompensate for the angle and tilt of the compression device. If theaccelerometer is not perfectly level on the chest of the victim and itsmovement is not perfectly vertical, errors will accumulate and must beaccounted for by the angle of the two horizontal axes. Certaincommercial products currently use accelerometer technology, such as theAED PLUS D-PADZ from Zoll Medical, in which the accelerometer isembedded into the pads of the defibrillator. Due to the additionalcircuitry and sensory within them, these defibrillator pads aresubstantially more expensive and must be disposed of after each use.Therefore, relatively expensive sensory must be routinely discarded dueto the design of the product.

Currently, a widely used technology in the training environment is theCPR mannequin. One commonly used version is the RESUSCI-ANNE dollmanufactured by Laerdal Medical Inc. The RESUSCI-ANNE doll allows anindividual to practice his or her CPR while being subjectively monitoredby an instructor. This technique relies on the observational skills ofthe instructor and thus may be prone to human error. Furthermore, foreffective training to take place, each student must be observedseparately thereby occupying a significant amount of time and decreasingthe number of students who can be trained at one time. In addition,Actar Airforce Inc. develops ACTAR mannequins providing limited feedbackthat are currently also used in CPR training. Again, such mannequinsrely on close monitoring by the instructor to be effective for training.

It would still be desirable to provide an easy-to-use and inexpensivedevice to accurately measure relevant CPR parameters such as compressiondepth and rate absent of the problems in the aforementionedtechnologies.

SUMMARY

Embodiments of invention are directed to methods and devices for thedetermination and calculation of the depth of chest compressions duringthe administration of cardiopulmonary resuscitation (CPR). Embodimentsinclude the use of optical sensors to monitor the distance that avictim's chest is displaced during each compression throughout theadministration of CPR. The optical sensor is most commonly an imagesensor such as CMOS or CCD sensor, and more, in some specificembodiments can be a CMOS image sensor capable of three-dimensionalimaging based on the time-of-flight principle. However, otherembodiments may include other traditional optical sensors such asinfrared, optical proximity, LED, optical flow or laser-basedtechnologies. Those skilled in the art will appreciate that, while thepreferred sensor is desirably a time-of-flight depth sensor, this is nota requirement of the invention. Other sensors capable of detecting theposition of an object in three-dimensional space may be used withoutdeparting from the spirit of the inventive principles disclosed herein.

In the case of image sensors, the sensor may be placed on the rescuer orin a device external to the rescuer, such as a block or pad. If placedon the rescuer, the sensor may be located in any of a number ofpositions. In one embodiment, the sensor may be placed in a glove wornby the rescuer and the glove may position the sensor on the posteriorsurface of the forearm. The image sensor may be directed so that thepixels of the sensor are pointed downward enabling visualization of aportion of the victim's body as well as the ground beneath the victim.An infrared emitter may be positioned adjacent to the image sensor toilluminate the victim's body and any visible piece of ground beside thevictim. As the infrared light interacts with the surfaces it encounters,it is reflected and returns to the image sensor where the time of flightof the infrared light is calculated for every pixel in the image sensor.This distance data is used to gauge the effective displacement of therescuer's hand and arm relative to a non-moving surface such as theground or a stationary portion of the victim, such as the shoulders,head, neck, stomach or legs.

In another embodiment of the invention, an image sensor is placed on theposterior surface of the forearm but is positioned toward the rescuer'storso rather than the torso of the victim. The image sensor isconfigured so that it may determine the depth of a compression bymonitoring the optical flow of its environment, such as the change inpattern of the rescuer's stationary upper body. The optical flow methodcan also be used to track changes in other stationary features of therescuer's environment, such as walls or immobile objects, and relatethese to the depth of each compression.

Rather than being configured within a wearable device on the rescuer,embodiments of the invention may also be incorporated into a block, pador other device placed under the hands of the rescuer performing theCPR. The image or optical sensor may be directed toward the chest of thevictim, toward the torso of the rescuer or toward the environment totrack optical changes and relate these to the depth of each chestcompression.

In another embodiment, the optical sensor may be placed on a deviceindependent of the rescuer. The image sensor or optical sensor may beplaced on a stationary support positioned above the chest of the victimand over the hands of the rescuer. The sensor may then determine thedepth of each compression by reflecting infrared light from the victimand rescuer and using time-of-flight calculations or other techniques togauge compression depth.

The use of optical compression depth techniques also has applications inCPR training. The device may be used to accurately gauge compressiondepth while training individuals in CPR. This technique is highlyaccurate and can be used to properly train individuals to administer CPRat the proper depth, a common problem plaguing many rescuers.

Furthermore, optical compression depth techniques have furtheradvantages. Unlike the use of gyroscope or accelerometer based sensors,optical techniques do not suffer from cumulative error and do not relyon inertial measurements that can be affected by the surroundingenvironment. When using accelerometers, the victim and rescuer must notexperience any external movement such as that caused by transport of thevictim in an ambulance or helicopter. Such random and non-isolatedmovements of the patient will invalidate any measurements taken byinertial sensors. Furthermore, optical sensor techniques have theadvantage of being useful in a wide-array of CPR related measurementsnot limited to compression depth. The optical sensors can be used tovisualize the size of a patient and immediately gauge the body type andinstruct the user accordingly. For instance, there is a significantdifference between infant and adult CPR and automatic body typecompensation algorithms are highly beneficial in a fast-moving emergencywhere every second matters. Furthermore, optical measurement techniquescan be used to accurately measure chest rise during artificialrespiration and ensure that proper ventilation is being administered inbetween compressions. In addition, optical measurements of the chest ofthe victim and the hands of the rescuer can help ensure that the rescuerhas positioned his or her hands in the anatomically correct location foreffective CPR.

Optical compression depth measurement techniques are a highly accurateand likely inexpensive method of determining compression depth duringthe administration of CPR. Optical methods do not suffer from thedrawbacks of accelerometer-based techniques. They are inherently moreaccurate as they do not experience cumulative errors or inaccuracies dueto movement of the victim or rescuer.

BRIEF DESCRIPTION OF THE DRAWINGS

Aspects of the present invention will be discussed in detail below, withreference to the drawings in which:

FIG. 1 shows a time-of-flight three-dimensional CMOS image sensor withinfrared illumination sources according to embodiments of the invention;

FIG. 2 illustrates the time-of-flight principle of operation for athree-dimensional image sensor that may be used in embodiments of theinvention;

FIG. 3 depicts an array of values representing the distance of an objectat each pixel of a three-dimensional image sensor, such as the imagesensor of FIG. 1;

FIG. 4 shows an example of a compression gradient according toembodiments of the invention;

FIG. 5 depicts a wearable embodiment of a three-dimensional image sensorin which the sensor is attached to the arm of the rescuer according toembodiments of the invention;

FIG. 6 shows an external block housing a three-dimensional image sensorthat may be placed under and around the hands of the rescuer during theadministration of CPR according to embodiments of the invention;

FIG. 7 shows an external support stand housing a three-dimensional imagesensor that may be positioned over the victim's torso according toembodiments of the invention;

FIG. 8 shows an automatic external defibrillator that may house athree-dimensional image sensor according to embodiments of theinvention;

FIG. 9 illustrates a three-dimensional image sensor on a swinging pivotaccording to embodiments of the invention;

FIG. 10 depicts an image sensor affixed the arm of a rescuer for thedetermination of optical flow according to embodiments of the invention;

FIG. 11 illustrates the isolation of various regions of the victim fromthe effects of a chest compression according to embodiments of theinvention;

FIG. 12 shows an accelerometer adjacent to an image sensor for thedetermination of compression angle according to embodiments of theinvention;

FIG. 13 shows a rescuer performing CPR with a proper compression angleof approximately ninety degrees according to embodiments of theinvention;

FIG. 14 illustrates the proper placement of the rescuer's hands duringthe administration of CPR;

FIG. 15 illustrates the various measurements that may be carried out bya three dimensional image sensor on the victim's body according toembodiments of the invention;

FIG. 16 shows the direction of chest rise during the administration ofrescue breathing;

FIG. 17 shows a wearable arm band that may house a three-dimensionalimage sensor according to embodiments of the invention; and

FIGS. 18-22 illustrate various methods that may be performed accordingto embodiments of the invention.

DETAILED DESCRIPTION OF THE INVENTION

An image sensor is a device that converts an optical image to anelectric signal. The two most widely recognized types of image sensorsare the (Complementary Metal Oxide Semiconductor) CMOS and CCD (ChargeCoupled Device) sensors. A CMOS chip is a type of active pixel sensormade using the CMOS semiconductor process. Extra circuitry next to eachpixel sensor converts the light energy to a voltage. Additionalcircuitry on the chip converts the voltage to digital data. A CCD is ananalog device. When light strikes the chip it is held as a smallelectrical charge in each pixel sensor. The charges are converted tovoltage one pixel at a time as they are read from the chip. Additionalcircuitry in the camera converts the voltage into digital information.

A CMOS image sensor 1 is illustrated in FIG. 1 Along with an infraredillumination source 2, the image sensor 1 determines thethree-dimensional characteristics of a scene by measuring thetime-of-flight of the illumination from the infrared source 2. Recentadvances have allowed one-chip solutions that enable the capturing andprocessing of real-time three dimensional images and video. The smallCMOS sensor 1 determines the distance to objects in the environment withmillimeter accuracy while maintaining fast frame rates. Suchthree-dimensional images are invaluable to areas requiring real-timeprecision depth or distance measurement. One application that canbenefit enormously from such a technology is chest compressionmonitoring during the administration of CPR. Output from the sensor 1may be passed to other processing circuitry known in the art tocalculate desired outputs or control signals. For instance theprocessing circuitry may include timers, counters, Arithmetic LogicUnits (ALUs), programmed processors etc. for generating the outputs usedin other parts of the system. Conversely, some or all of these functionsmay take place on or in what is illustrated as the sensor 1.

One application of time-of-flight optical sensors in the monitoring ofCPR is the accurate determination of chest compression depth. Otherembodiments additionally determine other parameters useful in evaluatingthe efficacy of the CPR being performed. Time-of-flight optical sensorshave a wide range of possibilities in CPR including determination of:compression rate, victim body type, efficient rescue breathing, handpositioning during compressions, and chest recoil. This new technologyhas the potential to revolutionize the delivery of CPR, making it anefficient and accurate procedure free from any significant human error.

Determination of Compression Depth A. Time-of-Flight Measurement

In a preferred embodiment, the present invention utilizes the CMOS imagesensor 1, an illuminating source 2 such as an infrared light emittingdiode (LED) and processing circuitry to compute compression depth. Inthis embodiment, the CMOS sensor 1 and accompanying circuitry functionsimilar to radar. The distance to an object is calculated using ameasurement of time that it takes an electronic burst of unobtrusivelight or invisible (yet detectable) energy 3 to make the round trip froma the transmitter 4 to the reflective object 5 and back as shown in FIG.2. The image sensor 1 is completely or mostly immune to ambient lightand is able to independently, or along with other circuitry, internallydetermine the length of time taken by the pulse to reflect back to eachpixel, using high speed, on-chip timers or by simply measuring thenumber of returning photons. The result is an array of distances 6 thatprovides a mathematically accurate, dynamic relief map 7 of the surfacesbeing imaged as shown in FIG. 3. The image and distance information isthen processed to further refine the three dimensional representationbefore being used to compute compression depth information.

The time-of-flight distance data is used to construct a compressiongradient, a representation of which is shown in FIG. 4. A compressiongradient is a detailed three dimensional map of the rescuer's hand 8, aportion of the victim's body 9 and preferably a portion of the groundbeneath the victim 10. This compression gradient is important toextracting the depth information of each chest compression. Infraredlight 3 is emitted from an illumination source 2 or multipleillumination sources adjacent to the image sensor 1. The light isinvisible to the naked eye and generally immune to ambient interference.When affixed to the arm of the rescuer as shown in FIG. 5, the imagesensor 1 receives the infrared light 3 reflected from the victim's bodyand the ground. A chest compression compresses the ribs, sternum andchest of the victim but generally leaves the stomach, neck and head ofthe victim substantially unmoved. Furthermore, the ground 10 or surfacebeneath the victim generally remains stationary during a compression.The system including the sensor 1 makes a determination of the qualityof a compression by analyzing the generated gradient. The stationaryportions of the victim and ground 10 will move closer to the sensor asthe compression progresses downward. However, the hands of the rescuer 8as well as the portion of the chest of the victim 11 adjacent and underthe hand of the rescuer will remain stationary relative to the sensor.Therefore, the hands of the user 8 and chest of the victim 11 willappear deeper in the gradient than the stationary portions of the image.Once the rescuer's hand reaches the bottom of the compression, it willbegin to move upward again and the stationary parts of the victim andthe ground will appear to move away from the sensor. This gradientinformation can be used to accurately determine the depth of thecompression.

At the start of the chest compression, the stationary aspects of theimage will be furthest away from the image sensor. As the compressiontravels deeper, those stationary aspects such as the ground 10 andvictim's anatomy will travel toward the sensor. Therefore, the algorithmcontinually searches for stationary aspects by finding adjacent pixelsof a similar distance. The on-board processor isolates these blocks andtracks their distance relative to the arm 12 of the rescuer on which thesensor resides. If the image sensor 1 finds an area of ground beneath 10the victim, it will track the distance of the ground relative to thesensor. If it finds a portion of the victim's stomach, it will track thedistance of the stomach relative to the sensor. Any nonmoving surfacemay provide a suitable reference point.

The image sensor 1 may be mounted on the arm 12 of the rescuer, asdiscussed above, or may be mounted inside a device 13 partially or fullyunder or around the rescuer's hands as show in FIG. 6. The sensor 1 mayinstead be mounted above the body of the victim using an externalsupport or stand 14 as shown in FIG. 7. The image sensor 1 can also beplaced in an external unit 15 beside the patient, such as adefibrillator, that is positioned so that the image sensor 1 may monitorthe compression as shown in FIG. 8. The sensor 1 may also be placed on apivot 16 to ensure that is constantly points in the same direction andis not affected by unpredictable movements of the rescuer's arm 12 orthe victim's body 9 as shown in FIG. 9.

The image sensor 1 used may be a three dimensional time-of-flight CMOSsensor fabricated for the purpose of distance determination as seen inU.S. Pat. No. 6,323,942, which is incorporated by reference herein.Certain suitable sensors currently on the market include theCANESTAVISION PERCEPTION chipset from Canesta, the PHOTON ICs from PMDTechnologies GmbH, and the SWISSRANGER sensors from Mesa Imaging. Thethree-dimensional imaging may also be accomplished by stereo visionthrough the algorithmic processing and combining of the input from twodistinct image sensors.

B. Optical Flow Measurement

Another method of determining compression depth involves the use ofoptical flow techniques in which an image sensor monitors thesurrounding environment to track the movement of textures and patterns.The image sensor may be mounted on the posterior surface of the forearm17 of the rescuer and aimed at the torso 18 of the rescuer as shown inFIG. 10. As the compression is initiated, the sensor will move downward,but the torso 18 of the rescuer will generally remain stationary.Therefore, the image sensor 1 will monitor patterns or unique aspects ofthe torso 18 of the rescuer and correlate the movement of these patternsto the movement of the sensor 1 and thus the movement of the rescuer'sarm 12. The depth of a chest compression can then be determined byrelating the movement of the rescuer's arm to the movement of thevictim's chest.

This method employed for the optical flow technique is similar to thatfound in optical computer mice that employ an image sensor for trackingthe patterns and features of the surface on which the mouse is used.Using a relatively high resolution image sensor, distinct features maybe tracked at a very high frame rate. As the feature moves past theimage sensor, a distance is calculated based on the frame rate anddistance traveled of that specific feature being tracked. This distanceand speed is then translated into the speed and distance traveled by therescuer's hand through the entirety of the chest compression.

Generation of a Compression Gradient

During the calculation of most CPR related parameters usingtime-of-flight three dimensional image sensors, a compression gradientor similar depth map may be generated by, for instance, the processingcircuitry.

The time-of-flight distance data from the image sensor is used toconstruct a compression gradient. A compression gradient is a detailedthree dimensional map of the rescuer's hand, a portion of the victim'sbody and preferably a portion of the ground beneath the victim. Thiscompression gradient is a base for extracting the depth information ofeach chest compression.

The compression gradient consists of a contour map of the victim's bodyoriginating at the site of the chest compression and radiating outward.The pixels of the image sensor visualizing an area closest 19 to thesite of the compression will be most affected by the compression itselfand the pixels visualizing an area furthest 20 from the site of thecompression will be least affected by the compression as shown in FIG.11. In a preferred embodiment, the image sensor will move with therescuer's hands through the entire distance of the compression and,consequently, the pixels nearest to the site of the compression shouldmeasure a constant or nearly constant depth. The pixels furthest awayfrom the site of the compression should measure the largest change indepth as they will be moving toward the sensor as the compressionprogresses downward and away from the sensor as the compression isreleased. Therefore, the pixels furthest away from the site of thecompression are deemed to be the stationary components of the scene (thevictim's shoulders, the ground beneath the victim, etc.).

Therefore, a compression gradient is a depth contoured map of thevictim's body 9, the ground 10 or surface beneath the victim and aportion of the hands 8 of the rescuer at the site of the compression.The compression gradient shows the distance or relative distance fromthe image sensor to the victim and ground at any instance in time forevery pixel in the sensor. A processor or controller weighs theimportance of that pixel's information by how isolated it is from theincident site of the compression. If a certain set of pixels is imagingthe ground around the victim, for example, the processor determines thatthis is an important stationary reference point that can be used tocalculate the depth of the chest compressions. Stationary points in theenvironment appear to move relative to the image sensor as it travelsduring the course of the chest compression. It is these stationaryreference points that allow compression depth to be most preciselycalculated.

An example method of generating a compression gradient is illustrated inFIG. 18. In the illustrated method, a starting or baseline image isobtained by the sensor 1 in a process 50. Then a compression begins in aprocess 52. A distance between the sensor and the image viewing area ofthe sensor is tracked during the chest compression in a process 54, and,in a process 56, a gradient is calculated based on the data generated bythe image sensor. In some embodiments data from a timer may be used aswell.

Determination of Compression Rate

Calculating the rate of compressions delivered during the administrationof CPR may be accomplished with the use of an image sensor 1. Thegeneration of a compression gradient with time-of-flight principlesallows for the determination of the initiation and termination of asingle chest compression. A processor or controller may determine when achest compression has passed through both its maximum and minimum depthsand may register this as a single event. Therefore, a device using animage sensor as a compression monitor may indicate to the rescuer atwhat rate the CPR is being performed and how many chest compressions maybe remaining in a certain chest compression cycle. Internationalguidelines indicate that CPR should be performed at a rate of 100compressions per minute and that there should be thirty compressions forevery two breaths in each cycle.

An example method of determining a compression rate is illustrated inFIG. 19. In the illustrated method, a starting or baseline image isobtained by the sensor 1 in a process 60. Then a compression begins in aprocess 62. At the time of the maximum compression, a timer state isrecorded in a process 64, and the timer state at a moment of maximumrelease is also recorded in a process 66. In a process 68, a processoruses the relative times from the maximum and minimum times to generate arate of chest compressions, or CPR rate, the processes 64-68 may berepeated to generate an average compression rate.

Determination of Compression Angle

Compression angle 22 may be monitored by placing an accelerometer 21,tilt sensor or other device alongside the image sensor in a CPR assistdevice as shown in FIG. 12. The compression angle sensor would enablethe CPR assist device to alert the rescuer if he or she must adjust hisor her arms to achieve a proper chest compression angle. When deliveringeffective CPR, the hands of the rescuer 8 should be approximatelyperpendicular to the arms of the rescuer 12 as shown in FIG. 13.Furthermore, ensuring that the arms are perpendicular to the chest ofthe victim will help make certain that the image sensor is properlyoriented. In the case that the arms are not at a right angle to thevictim's chest, the sensor and infrared light source 2 can be placed ona swinging pivot 16 that changes it direction to compensate for theangle of the arms.

Compression angle may be determined by the image sensor 1 itself. If theimage sensor 1 is affixed to the arm of the rescuer 12, trigonometriccalculations may be used to determine the angle 22 that the sensor isoriented relative to a level, planar surface such as the ground 10beneath the victim. The distances between the various pixels of theimage sensor 1 and objects within the environment can be determined andcompared. Relative to the ground or some level surface, an angle ofcompression can be easily determined.

Determination of Proper CPR Hand Position

Proper hand placement during CPR is vital to restoring circulation tothe victim. If the rescuer's hands are not appropriately positioned overthe sternum of the victim, the CPR will not be performed at its maximumefficiency and injury may result. Therefore, the determination of properhand placement is vital to the delivery of accurate and efficient CPR.

Correct CPR hand position 23 is determined by locating a positionapproximately two inches directly above the victim's xyphoid process 24where the lower ribs meet the sternum as shown in FIG. 14. The rescuer'shands 8 should be centered laterally on the chest between the shoulders25 of the victim. In order to determine the lateral centering 26, theimage sensor 1 may calculate the distance between the opposing shoulders25 of the victim and easily conclude the center 26 from thisinformation. The location of the xyphoid process 24 is substantiallymore difficult and relies on a calculation of the overall size of thepatient, as explained below. Once the approximate size of the patient isdetermined, the position of the victim's ribs and xyphoid process 24 maybe interpolated, allowing the sensor to determine if the rescuer's hands8 are in the general locale of the sternum. Rather than preciselyindicating position to the rescuer, the device will alert the user ifhis or her hand position is clearly off mark by a statisticallysignificant amount.

An example method of determining proper hand placement is illustrated inFIG. 20. In the illustrated method, a starting or baseline image isobtained by the sensor 1 in a process 70. Then a hand position of therescuer is determined by analyzing data and/or images from the imagesensor in a process 72. A process 74 locates the xyphoid process of thepatient, or an area near the xyphoid process, and a process 76determines if the hand position of the rescuer is near the appropriateposition of the xyphoid process of the victim. The determination of handposition may be related back to the rescuer in a process 78.

Determination of Victim Body Type

An image sensor for detection of compression depth may also have theinherent capability of determining body size and body type as shown inFIG. 15. An image sensor 1 suspended above the victim's body 9 maylocate the contours 27 of the body, as well as its size and the depth 28to the ground beneath it.

Suspended above the victim's body, the image sensor 1 is capable ofdetermining specific parameters related to the body type of the victim.Such parameters include shoulder to shoulder width 29, torso length 30,depth of chest to ground 28, arm length 31, neck width 32 and others. Byuniquely combining these elements, it is possible to determine theapproximate size of the victim. Upon determination of the victim bodytype, the CPR protocol may be adjusted accordingly.

The determination of body type is especially important in child andinfant CPR where the depth of compressions should be directly correlatedto the depth of the chest of the child. For example, if compressionsshould be one-third to one-half the total anteroposterior diameter ofthe chest, the image sensor can quickly calculate this dimension andensure that the advised compression depth is in accordance with thechild's size. This will ensure that CPR is delivered appropriately for avictim of any body size from the smallest infant to the largest adult.

An example method of determining patient body type is illustrated inFIG. 21. In the illustrated method, a patient image is gathered by thesensor in a process 80. A process 82 determines patient parameters fromthe image, such as shoulder width, torso length, depth of chest toground, arm length, neck width, etc. Then, one or more of the parametersare compared to a database or history of previously stored parameters orset of comparisons or determinations in a process 84. This comparison ordetermination allows the system to determine the proper body type.

Determination of Effective Rescue Breathing

The image sensor may be used for the detection of chest rise 33 duringthe administration of artificial respiration as shown in FIG. 16. Ifsuspended above the patient, a three dimensional gradient may begenerated similar to a compression gradient. This gradient may be usedto determine if the chest of the victim rises during rescue breathingand to what extent the chest rises. This information may be used todetermine if a successful breath has been administered. Such methods areillustrated in FIG. 22. In that figure, a starting image is recorded inprocess 90 and a gradient is generated in process 92 based on the chestrising due to rescue breaths, as described above. Data about the rescuebreaths is recorded in process 94, such as the amount of the victim'schest rising and the amount of time between rescue breaths. Thecollected data is compared to stored data in a process 96, which maythen determine if the rescue breathing is effective.

Determination of Chest Recoil

The image sensor may also be used to determine if the chest hascompletely recoiled during the administration of CPR. After a chestcompression attains the desired depth, the victim's chest should bereleased fully and completely before commencing the next compression. Acompression gradient may be used to determine if the chest has beenallowed to fully recoil by measuring the depth of the rescuer's hands 8relative to the victim's torso 9 and ground 10.

Potential Embodiments

The measurement of compression depth with optical sensors may beemployed in various embodiments not limited by the specificationsdisclosed herein. For example, the sensor may be wearable in the form ofa glove, wrist band shown in FIG. 17, wrist guard shown in FIG. 5 or anyother type of garment on the rescuer. The sensor may also be housed in asolid block, pad or similar device placed beneath the hands of therescuer. The sensor may be placed on an independent support or stand tobe suspended above the patient. The sensor may also be placed withinanother piece of equipment, such as a defibrillator.

When configured in a block or pad, the optical sensor should be elevatedabove the chest of the victim so that it may image a large enoughportion of the victim's chest and the ground beneath the victim. Thesensor may be configured so that it is raised above the hands of therescuer and body of the victim. When configured in an external supportor stand, the sensor may be elevated high above the victim and rescuerallowing visualization of a larger portion of the ground, victim's bodyand rescuer's hands. The stand may be completely independent of thevictim and rescuer and may be positioned adjacent to the victim so thatthe image sensor is elevated and suspended above the victim.

In embodiments of the invention, the device may have a method offeedback or the methods may incorporate feedback within them. Forexample, if the image sensor is placed within a block, a numerical orgraphical display 34 may be embedded opposite the sensor so that visualdata is relayed to the rescuer. Furthermore, audio feedback may beembedded into the device to complement or replace the visual feedback.In many embodiments of the invention, there is an optical sensor used toimage a portion of the victim or rescuer. In the preferred embodiment ofthree-dimensional time-of-flight sensors, the optical sensor is pointeddownward, toward the victim, to allow for optimal visualization of thevictim, ground and rescuer's hands. Ultimately, the generation of acompression gradient allows for the determination of most crucial CPRrelated parameters.

1. A device for monitoring compressions during the administration ofcardiopulmonary resuscitation comprising an optical sensor.
 2. Thedevice of claim 1 wherein said optical sensor is used to determine thedepth of chest compressions during the administration of saidcardiopulmonary resuscitation.
 3. The device of claim 2 wherein saidoptical sensor is an image sensor.
 4. The device of claim 3 wherein saidimage sensor is structured to process three dimensional images of therescue environment.
 5. The device of claim 4 wherein said image sensoruses time-of-flight measurement to generate said three dimensionalimages.
 6. The device of claim 3 wherein said image sensor is used toperform optical flow calculations.
 7. The device of claim 1 wherein saidoptical sensor is used for the determination of compression rate duringthe administration of cardiopulmonary resuscitation.
 8. The device ofclaim 7 wherein said optical sensor is capable of processing threedimensional images.
 9. The device of claim 8 wherein said image sensoruses time-of-flight measurement to generate said three dimensionalimages.
 10. The device of claim 1 wherein said optical sensor is usedfor the determination of victim body type and victim body size.
 11. Thedevice of claim 10 wherein said optical sensor is capable of processingthree dimensional images.
 12. The device of claim 11 wherein said imagesensor uses time-of-flight measurements to generate said threedimensional images.
 13. The device of claim 12 wherein said body typeand body size is any of adult, child or infant.
 14. The device of claim1 wherein said optical sensor is used for the determination of properhand placement of the rescuer during the administration of saidcardiopulmonary resuscitation.
 15. The device of claim 14 wherein saidoptical sensor is capable of processing three dimensional images. 16.The device of claim 15 wherein said image sensor uses time-of-flightmeasurements to generate said three dimensional images.
 17. The deviceof claim 16 wherein the determination of proper hand placement of therescuer comprises determining whether the position of the hand of therescuer is slightly above the xyphoid process of said victim.
 18. Thedevice of claim 1 wherein said optical sensor is used to determine theadequate chest recoil of the victim during the administration of saidcardiopulmonary resuscitation.
 19. The device of claim 18 wherein saidoptical sensor is capable of processing three dimensional images. 20.The device of claim 19 wherein said image sensor uses time-of-flightmeasurement to generate said three dimensional images.
 21. The device ofclaim 20 wherein said adequate chest recoil constitutes allowing therescuer fully releasing the chest of the victim following each chestcompression.
 22. The device of claim 1 wherein said optical sensor isused to determine the delivery of adequate rescue breathing to thevictim.
 23. The device of claim 22 wherein said optical sensor iscapable of processing three dimensional images.
 24. The device of claim23 wherein said image sensor uses time-of-flight measurement to generatesaid three dimensional images.
 25. The device of claim 24 wherein saidadequate rescue breathing is determined by sensing the movement of thechest of said victim during the delivery of said rescue breathing. 26.The device of claim 1 wherein said optical sensor is configured to bewearable by the rescuer.
 27. The device of claim 1 wherein said opticalsensor is external to the rescuer.
 28. The device of claim 1 whereinsaid optical sensor is in a block or pad to be placed on the chest ofthe victim and under or around the hands of the rescuer.
 29. The deviceof claim 1 wherein said optical sensor is used to measure the opticalflow of the environment.
 30. The device of claim 1 wherein said opticalsensor is any of CMOS, CCD or other image sensor type.
 31. The device ofclaim 1 wherein said optical sensor is a three dimensional time-offlight image sensor.
 32. The device of claim 1 wherein an illuminationsource is positioned adjacent to said optical sensor.
 33. The device ofclaim 32 wherein said illumination source consists of infrared lightemitting diodes.
 34. The device of claim 33 wherein said illuminationsource consists of an infrared laser source.
 35. The device of claim 34wherein said illumination source is incident on the victim and reflectedback to said optical sensor for the generation of a depth map of saidvictim.
 36. The device of claim 1 further comprising a feedbackmechanism to deliver information to the user.
 37. The device of claim 36wherein the feedback information is audible.
 38. The device of claim 36wherein the feedback information is visual.
 39. The device of claim 37wherein the feedback is via a computer.
 40. The device of claim 37wherein said monitoring of chest compressions is for the purpose oftraining an individual in proper CPR technique.
 41. A method for thedetermination of the depth of chest compressions during theadministration of cardiopulmonary resuscitation comprising generating aninput from an optical sensor.
 42. The method of claim 41 wherein saidoptical sensor is an image sensor.
 43. The method of claim 42 furthercomprising generating distance values for each pixel of said imagesensor using time-of-flight principles.
 44. The method of claim 43further comprising using the generated distance values to determine saiddepth of chest compressions.
 45. The method of claim 41 wherein saidimage sensor is used to follow the movement of objects in itsenvironment and relate their movement to said depth of compressions.